Needleless medical connector with expandable valve mechanism

ABSTRACT

A needleless connector for medical use, adapted to facilitate the flow of fluid therethrough, includes a housing having an inlet port and an outlet port. The connector also includes a flex-tube assembly defining a fluid path between the inlet port and the outlet port. The flex-tube assembly is movable between uncompressed and compressed states. The flex-tube assembly has a first internal volume when in the uncompressed state and a second internal volume, greater than or substantially equal to the first internal volume, when in the compressed state.

BACKGROUND OF THE INVENTION

The invention relates generally to medical connectors of the type usedin the handling and administration of parenteral fluids, and moreparticularly, to a needleless connector employing a valve mechanism thatcompensates for negative fluid displacement, i.e., drawing of fluid intothe outlet end of a connector, during deactuation of the valve.

Within this specification the terms, “negative-bolus effect,”“positive-bolus effect,” and “no-bolus effect” are used to describe theoperating characteristics of medical connectors during deactuation ofthe valve mechanisms contained within the connectors. Negative-boluseffect describes the condition during which fluid is drawn into theconnector during deactuation. Positive-bolus effect describes thecondition during which fluid is flushed out of the connector duringdeactuation. No-bolus effect describes the condition during which fluiddisplacement is neutralized and fluid is neither drawn into nor flushedout of the connector during deactuation.

Needleless medical connectors for injecting fluid into or removing fluidfrom an intravenous (IV) system are well known and widely used.Conventional needleless medical connectors generally include a housinghaving an inlet port and an outlet port. The inlet port is sized toreceive a blunt male cannula, such as a male Luer taper. Disposed withinthe inlet port is a valve mechanism that provides access to a fluid paththat communicates with the outlet port. In some connectors, the fluidpath is defined by the internal boundaries of the connector housing, inother connectors it is defined by an internal cannula or hollow spike,still in others, the fluid path is defined by a compressible tubularbody which carries the valve mechanism. The outlet port of the connectoris typically connected to IV tubing which in turn is connected to an IVcatheter that communicates with a patient's venous system.

Many needleless medical connectors create fluid displacement duringactuation and deactuation of the valve mechanism. During actuation, theblunt male cannula is inserted into the inlet. In some connectors, thecannula passes through the valve mechanism to establish fluidcommunication with the fluid path. In other connectors, the cannulamerely displaces the valve mechanism, without penetrating it, in orderto establish fluid communication with the fluid path. In either case,the volumetric capacity of the fluid path is often reduced by theinsertion of the blunt cannula. Subsequently, when the blunt cannula isremoved from the connector, the volumetric capacity of the fluid pathincreases. This increase in the volumetric capacity may create a partialvacuum in the fluid path that may draw fluid into the connector from theoutlet end. As previously mentioned, the effect of drawing fluid intothe connector in this manner is referred to as a “negative-bolus” effectin that a quantity, or “bolus,” of fluid is drawn into the partialvacuum or negative pressure location; i.e., the connector.

A negative-bolus effect is undesirable in that the partial vacuumcreated within the connector may draw fluid from the IV tubing. The IVtubing in turn draws fluid from the IV catheter which in turn drawsfluid, e.g., blood, from the patient's venous system.

The negative-bolus effect may be reduced by undertaking operationalsafeguards. For instance, prior to the removal of the blunt cannula fromthe connector, the IV tubing may be clamped off between the connectoroutput port and the IV catheter. This prevents the backup of bloodthrough the IV catheter. If a syringe with a blunt cannula tip is usedto inject fluid into the inlet port of the valve, the syringe may becontinually depressed while the syringe is disengaged from theconnector. The continued depression of the syringe injects fluid intothe fluid path to fill the increasing volume thereby reducing the chanceof a partial vacuum forming in the fluid path and a negative bolus.However, both of these approaches are undesirable in that the operatormust remember to perform an additional step during removal of thesyringe or other device from the connector rather than the steps beingtaken automatically by the connector.

The negative-bolus effect may also be reduced by the design of themedical connector. As previously mentioned, some medical connectorsinclude an internal cannula or hollow spike housed inside the connectorbody. The internal cannula or spike is positioned to open a septum upondepression of the septum onto the internal cannula or spike by a bluntcannula. The internal cannula or spike has a small orifice at the topand upon depression of the septum is put in fluid communication with theblunt cannula. The internal cannula or spike provides a generallyfixed-volume fluid-flow path through the connector. Thus, as the septumreturns to its closed position the partial vacuum formed within theconnector is not as strong as the vacuum formed in a connector having amore volumetrically dynamic fluid path. A disadvantage of typicalconnectors having an internal cannula or spike is a lower fluid-flowrate. This low flow rate is caused by the small orifice in the cannulaor spike. Additionally, it has been noted that with the connector designhaving a fixedly-mounted internal spike and a movable septum that ispierced by that spike to permit fluid flow, such pierced septum may bedamaged with multiple uses and a leaking connector may result.

Other connectors provide a valve mechanism that includes a flexiblesilicone body and a rigid spring leaf positioned about an internalcannula. Upon depression of the valve mechanism by a blunt cannula, theinternal cannula forces the leaves of the spring leaf apart, the leavesin turn force the top of the body apart and open a slit containedtherein. The opening of the slit establishes fluid communication betweenthe blunt cannula and the internal cannula. The body includes a sidereservoir that expands upon depression of the valve mechanism andreceives fluid. Upon deactuation of the valve mechanism the reservoircollapses between the connector housing and the spring leaf and fluid isforced out of the reservoir into the internal cannula. This displacementof fluid may fill the partial vacuum being formed by the deactuation ofthe valve mechanism and thus reduce the possibility of fluid being drawninto the connector.

Although these connectors may reduce the negative-bolus effect, theyhave several disadvantages. First, during periods of nonuse, residualfluid left within the collapsed reservoir is likely to dry and adhere tothe leaf spring. This may cause particulate to enter the fluid pathduring subsequent actuation or may even prevent the reservoir fromexpanding during subsequent actuation. Second, the connector employs acomplex two-part valve mechanism that requires an internal cannula foractuation and deactuation. The complexity of this device lends itself tomanufacturing difficulties and increased manufacturing costs. Third,during actuation of the valve mechanism, the leaves of the rigid springleaf may cut through the body and cause a leak.

Hence, those concerned with the development of medical connectors haverecognized the need for a medical connector having a valve mechanismthat avoids the negative-bolus effect by producing either apositive-bolus effect or a no-bolus effect. The need for a medicalconnector that provides these effects without sacrificing fluid-flowrate or structural simplicity has also been recognized. The presentinvention fulfills such needs and others.

SUMMARY OF THE INVENTION

Briefly, and in general terms, the invention is directed to a medicalconnector having a valve mechanism that provides either a positive-boluseffect or a no-bolus effect, upon deactuation of the valve mechanism.

In a first aspect, the invention is directed to a needleless connectorfor medical use, adapted to facilitate the flow of fluid therethrough.The connector includes a housing having an inlet port and an outletport. The connector also includes a flex-tube assembly defining a fluidpath between the inlet port and the outlet port. The flex-tube assemblyis movable between uncompressed and compressed states and has a firstinternal volume when in the uncompressed state and a second internalvolume, at least as great as the first internal volume, when in thecompressed state.

By providing a flex-tube assembly having an internal volume whencompressed, e.g., activated by the insertion of a blunt cannula, that isat least as great as the internal volume when the flex-tube assembly isuncompressed, the possibility of a partial vacuum forming within thefluid path defined by the flex-tube assembly upon removal of the bluntcannula is essentially eliminated and instead, a positive-bolus effector a no-bolus effect is provided. Thus, fluid is prevented from beingdrawn into the connector through the outlet port upon removal of theblunt cannula.

In more detailed aspects, the second internal volume is greater than thefirst internal volume. In another detailed facet, the second internalvolume is substantially equal to the first internal volume. In yetanother detailed aspect, the flex-tube assembly includes an inlet endthat is positioned within the inlet port during the uncompressed stateand outside the inlet port during the compressed state. The flex-tubeassembly also includes a bore carried by the inlet end. The bore isclosed when the inlet end is within the inlet port and opened when theinlet end is outside the inlet port. In a further more detailed aspect,the flex-tube assembly includes a flex-tube insert having at least onecollapsible section movable between uncollapsed and collapsed states.The flex-tube assembly also includes a flex-tube piston that surroundsthe flex-tube insert and defines the fluid path. The flex-tube pistonincludes a piston head that is positioned within the inlet port duringthe uncompressed state and outside the inlet port during the compressedstate. The flex-tube piston also includes a bore that is carried by thepiston head. The bore is closed when the piston head is within the inletport and opened when the piston head is outside the inlet port. Theflex-tube piston further includes a piston base that is proximal theoutlet port and in communication therewith. The flex-tube piston isresponsive to the movement of the flex-tube insert. In another aspect,the flex-tube insert includes one collapsible section and the first endis secured within the piston head and the second end is secured withinthe piston base.

In yet another aspect, the flex-tube insert includes two collapsiblesections and a middle support for joining the two collapsible sections.For one collapsible section, the first end is secured within the pistonhead and the second end is pivotably attached to the middle support. Forthe other collapsible section, the first end is pivotably attached tothe middle support and the second end is secured within the piston base.In another facet, the flex-tube assembly includes at least onecollapsible section defining the fluid path, a piston head that ispositioned within the inlet port during the uncompressed state andoutside the inlet port during the compressed state, and a bore that iscarried by the piston head. The bore is closed when the piston head iswithin the inlet port and opened when the piston head is outside theinlet port. The flex-tube assembly also includes a piston base proximalthe outlet port and in communication therewith.

In yet another facet, the flex-tube assembly includes one collapsiblesection and the first end comprises the piston head and the second endcomprises the piston base. In still another facet, the flex-tubeassembly includes two collapsible sections and a middle support forjoining the two collapsible sections. For one collapsible section, thefirst end includes the piston head and the second end is pivotablyattached to the middle support. For the other collapsible section, thefirst end is pivotably attached to the middle support and the second endcomprises the piston base.

In a second aspect, the invention is related to a valve for providing afluid path between the inlet port and outlet port of a connector. Thevalve includes a flex-tube insert that is substantially axially alignedwith the axis of the fluid path. The insert is movable betweenuncompressed and compressed states and has a first maximum inner widthwhile uncompressed and a second maximum inner width, greater than thefirst maximum inner width, while compressed. The valve also includes aflex-tube piston surrounding the flex-tube insert and defining theradial boundaries of the fluid path. The flex-tube piston includes apiston head for positioning within the inlet port during theuncompressed state and outside the inlet port during the compressedstate. The flex-tube piston also includes a bore that is carried by thepiston head. The bore is closed when the piston head is within the inletport and opened when the piston head is outside the inlet port. Theflex-tube piston also includes a piston base for positioning proximalthe outlet port and providing fluid communication with the outlet port.The flex-tube piston is responsive to movement of the flex-tube insert.

In more detailed aspects, the flex-tube insert includes at least onecollapsible section having a maximum cross section when viewed along theaxis of the fluid path. The maximum cross section defines the first andsecond maximum inner widths. In another aspect, each collapsibleincludes a first end, a second end, and a plurality of hinge assemblies.Each hinge assembly has a hinge and two plates including twosubstantially parallel edges, one of the edges is attached to the hingefor pivotal movement and the other of the edges is attached to one ofeither the first or second ends for pivotal movement. In anotherdetailed facet, there are four hinge assemblies arranged so that theflex-tube insert has a substantially square cross section when viewedalong the axis of the fluid path and the distance between opposinghinges of the hinge assemblies define the first and second maximum crosssections.

In a third aspect, the invention is directed to a valve for providing afluid path between the inlet port and outlet port of a connector. Thevalve includes a collapsible section having a hollow interior definingthe radial boundaries of the fluid path. The collapsible section ismovable between uncompressed and compressed states and has a firstmaximum cross-sectional area while uncompressed and a second maximumcross-sectional area, greater than the first maximum cross-sectionalarea, while compressed. The valve also includes a piston head at one endof the collapsible section for positioning within the inlet port duringthe uncompressed state and outside the inlet port during the compressedstate and a bore carried by the piston head. The bore is closed when thepiston head is within the inlet port and opened and communicating withthe interior of the collapsible section when the piston head is outsidethe inlet port. The valve also includes a piston base at the other endof the collapsible section for positioning proximal the outlet port andproviding communication with the outlet port.

In a more detailed facet, the collapsible section includes at least onecollapsible portion having a maximum cross-sectional area when viewedalong the axis of the fluid path. The maximum cross-sectional areadefines the first and second maximum cross-sectional areas. In anotherfacet, each collapsible portion includes a first end, a second end, anda plurality of hinge assemblies. Each hinge has a hinge and two platesincluding two substantially parallel edges. One of the edges is attachedto the hinge for pivotal movement and the other of the edges is attachedto one of either the first or second ends for pivotal movement. Thecollapsible portion further includes a plurality of resilientlydeformable webs joining the edges of adjacent hinge assemblies to sealthe interior of the collapsible section. In a more detailed facet, thereare three hinge assemblies arranged so that the collapsible portion hasa substantially triangular cross section when viewed along the axis ofthe fluid path.

In a fourth aspect, the invention is related to a method of controllingthe flow of fluid between an inlet port and an outlet port of a medicalconnector having a valve assembly defining a fluid path having aninternal volume. The valve assembly has an inlet end disposed within theinlet port and an outlet end communicating with the outlet port. Theinlet end carries a bore that is closed when within the inlet end andopened when outside the inlet port. The method includes the steps ofincreasing the internal volume of the fluid path while simultaneouslyopening the bore and subsequently decreasing the internal volume of thefluid path while simultaneously closing the bore.

In a more detailed aspect, the valve assembly is formed of a resilientlydeformable material and the step of increasing the internal volume ofthe fluid path while opening the bore includes the steps of displacingthe inlet end from the inlet port and expanding the valve assembly in agenerally radial outward direction relative to the axis of the fluidflow path. In another aspect, the step of displacing the inlet end fromthe inlet port includes the step of inserting a male-Luer taper into theinlet port and applying pressure to the inlet end. In yet another facet,the step of decreasing the internal volume of the fluid path whileclosing the bore includes the steps of placing the inlet end in theinlet port and collapsing the valve assembly in a generally radialinward direction relative to the axis of the fluid flow path. In stillanother facet, the step of placing the inlet end in the inlet portcomprises the step of removing the male-Luer taper from the inlet port.

In a fifth aspect, the invention is directed to a method of controllingthe flow of fluid between an inlet port and an outlet port of a medicalconnector having an axially compressible valve assembly defining a fluidpath having an internal volume. The valve assembly has an inlet enddisposed within the inlet port and an outlet end communicating with theoutlet port. The inlet end carryies a bore that is closed when withinthe inlet end and opened when outside the inlet port. The methodincludes the steps of maintaining the internal volume of the fluid pathsubstantially constant while axially compressing the valve assembly andopening the bore; and subsequently maintaining the internal volume ofthe fluid path substantially constant while axially decompressing thevalve assembly and closing the bore.

In a sixth aspect, the invention is related to a connector for medicaluse, adapted to facilitate the flow of fluid therethrough. The connectorincludes an inlet port, an outlet port and a valve assembly defining afluid path between the inlet port and the outlet port. At least one ofthe inlet port, the outlet port and the valve assembly is formed toinclude an antimicrobial agent.

These and other aspects and advantages of the invention will becomeapparent from the following detailed description and the accompanyingdrawings, which illustrate by way of example the features of theinvention.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a perspective view of a medical connector that incorporatesaspects of the present invention;

FIG. 2 is an exploded perspective view of the medical connector shown inFIG. 1 depicting a valve body, a male Luer lock insert, and a flex-tubeassembly, i.e., valve assembly, including a flex-tube piston and aflex-tube insert;

FIG. 3 is a perspective view of the medical connector shown in FIG. 1with the valve body removed and depicting the flex-tube assemblypositioned on the male Luer lock insert;

FIG. 4 is perspective view of the male Luer lock insert shown in FIGS.1-3;

FIGS. 5a-5 d depict various views of the male Luer-lock insert shown inFIG. 4 including a side elevation view, a top plan view, a bottom planview and a full sectional view;

FIG. 6 is a perspective view of the valve body shown in FIG. 1;

FIGS. 7a-7 d depict various views of the valve body shown in FIGS. 2 and6 including a side elevation view, a top plan view, a bottom plan viewand a full sectional view;

FIG. 8a is a full sectional view of the flex-tube assembly shown inFIGS. 2 and 3 depicted in an uncompressed state and showing theflex-tube insert positioned within the flex-tube piston;

FIG. 8b is a top view of the flex-tube assembly shown in FIG. 8a takenalong the line 8 b—8 b;

FIG. 9a is a full sectional view of the flex-tube assembly shown inFIGS. 2 and 3 depicted in a compressed state and showing the flex-tubeinsert positioned within the flex-tube piston;

FIG. 9b is a top view of the flex-tube assembly shown in FIG. 9a takenalong the line 9 b—9 b;

FIG. 10 is a perspective view of the flex-tube insert shown in FIGS. 2,8 a, 8 b, 9 a, and 9 b;

FIG. 11a is a side elevation view and a top view of the flex-tube insertshown in FIG. 10;

FIG. 11b is a full sectional view of the flex-tube insert shown in FIG.10;

FIG. 12 is a perspective view of the flex-tube piston shown in FIGS. 2,3, 8 a and 8 b;

FIGS. 13a and 13 b are first and second full sectional views and topviews of the flex-tube piston shown in FIG. 12 with the views rotated 90degrees from each other;

FIG. 14 is a full sectional view of a positive-bolus configuration ofthe medical connector shown in FIG. 1 depicting the flex-tube assemblyin the uncompressed state;

FIG. 15 is a full sectional view of a positive-bolus configuration ofthe medical connector shown in FIG. 1 depicting the flex-tube assemblyin the compressed state under pressure of an inserted blunt orneedle-free cannula having a male Luer taper;

FIG. 15a is a graph depicting the volume of fluid within the flex-tubeassembly as a function of the depth of insertion of a blunt orneedle-free cannula into a medical connector providing a positive-boluseffect;

FIG. 16 is an elevation view of another medical connector thatincorporates aspects of the present invention;

FIG. 17a is a full sectional view of a flex-tube assembly incorporatedin the connector shown in FIG. 16 depicted in an uncompressed state andshowing the flex-tube insert positioned within and surrounded by theflex-tube piston;

FIG. 17b is a top view of the flex-tube assembly shown in FIG. 17a takenalong the line 17 b—17 b;

FIG. 18a is a full sectional view of the flex-tube assembly incorporatedin the connector shown in FIG. 16 depicted in a compressed state andshowing the flex-tube insert positioned within and surrounded by theflex-tube piston;

FIG. 18b is a top view of the flex-tube assembly shown in FIG. 18a takenalong the line 18 b—18 b;

FIG. 19 is a full sectional view of the medical connector shown in FIG.16 depicting the flex-tube assembly in the uncompressed state;

FIG. 20 is a full sectional view of the medical connector shown in FIG.16 depicting the flex-tube assembly in the compressed state;

FIG. 21 is an elevation view of another medical connector thatincorporates aspects of the present invention;

FIG. 21a is an exploded perspective view of the medical connector shownin FIG. 21 depicting a valve body, a male Luer lock insert, and aone-piece flex-tube assembly, i.e., valve assembly;

FIGS. 22a-22 d depict various views of the male Luer-lock insert shownin FIG. 21 including a side elevation view, a top plan view, a bottomplan view and a full sectional view;

FIG. 23 is a perspective view of the valve body shown in FIG. 21;

FIGS. 24a-24 d depict various views of the valve body shown in FIG. 23including a side elevation view, a top plan view, a bottom plan view anda full sectional view;

FIGS. 25a and 25 b are perspective views of the flex-tube assemblyhoused within the medical connector shown in FIG. 21, FIG. 25a depictsthe flex-tube assembly in an uncompressed state while FIG. 25b depictsit in a compressed state;

FIG. 26a and 26 b are first and second full sectional views and topviews of the flex-tube assembly shown in FIG. 25 with the views rotated90 degrees from each other;

FIG. 27a is a full sectional view of the flex-tube assembly shown inFIG. 25 depicted in an uncompressed state;

FIG. 27b is a top view of the flex-tube assembly shown in FIG. 27a takenalong the line 27 b—27 b;

FIG. 28a is a full sectional view of the flex-tube assembly shown inFIG. 25 depicted in an compressed state;

FIG. 28b is a top view of the flex-tube assembly of FIG. 28a taken alongthe line 28 b—28 b;

FIG. 29 is a full sectional view of a positive-bolus configuration ofthe medical connector of FIG. 21 depicting the flex-tube assembly in theuncompressed state;

FIG. 30 is a full sectional view of a positive-bolus configuration ofthe medical connector of FIG. 21 depicting the flex-tube assembly in thecompressed state under pressure of an inserted blunt or needle-freecannula having a male Luer taper;

FIG. 31 is an exploded perspective view of a medical connector thatincorporates aspects of the present invention, depicting a valve body, amale Luer-lock insert, and a one-piece flex-tube assembly, i.e., valveassembly;

FIG. 32 is a perspective view of the male Luer-lock insert shown in FIG.31;

FIGS. 33a-33 c depict various views of the male Luer-lock insert shownin FIG. 32, including a side elevation view, a top plan view, and a fullsectional view;

FIG. 34 is a perspective view of the valve body shown in FIG. 31;

FIGS. 35a-35 d depict various views of the valve body shown in FIG. 34,including a first side elevation view, a top plan view, a full sectionalview and a second side elevation view rotated 90 degrees relative thefirst side elevation view;

FIG. 36 is a perspective view of the flex-tube assembly in FIG. 31,depicting the flex-tube assembly in an uncompressed state;

FIGS. 37a-37 b are first and second full sectional views and top viewsof the flex-tube assembly shown in FIG. 36 with the views rotated 90degrees from each other;

FIG. 38a is a full sectional view of the flex-tube assembly shown inFIG. 36 depicted in an uncompressed state;

FIG. 38b is a top view of the flex-tube assembly shown in FIG. 38a takenalong the line 38 b—38 b;

FIG. 39a is a full sectional view of the flex-tube assembly shown inFIG. 36 depicted in an compressed state; and

FIG. 39b is a top view of the flex-tube assembly of FIG. 39a taken alongthe line 39 b—39 b.

DETAILED DESCRIPTION OF PREFERRED EMBODIMENTS

Referring now to the drawings in which like numerals refer to like orcorresponding elements among the several figures, there is illustratedin FIGS. 1, 16 and 21 several medical connectors that include aneedleless valve embodying aspects of the invention, These particularconnector configurations are for illustration purposes only. The subjectneedleless valve can be embodied in any of a variety of connectorsincluding, but not limited to, Y-connectors, J-loops, T-Connectors,Tri-connectors, PRN adapters, slip Luers, tubing engagement devices,access pins, vail adapters, blood tube adapters, bag access pins, andvented adapters.

As is shown in FIGS. 1 and 2, the connector 10 comprises a valve body 12having an inlet port 14. The connector 10 further includes a maleLuer-lock insert 16 terminating in an outlet port 18. The valve body 12and the male Luer-lock insert form a connector housing. The portion ofthe valve body 12 near the inlet port 14 includes a Luer adapter 20. Theadapter 20 is configured to receive all ANSI standard male Luerfittings, as well as other blunt cannulas or fluid conduit devices. Theconnector 10 also includes a resiliently deformable flex-tube assembly22, i.e., valve assembly, which includes a flex-tube insert 24 disposedwithin a flex-tube piston 26. As shown in FIGS. 3 and 4, the maleLuer-lock insert 16 includes a support post 28 for receiving theflex-tube assembly 22. The support post 28 has three vertical channels30 running the length of the post and terminating at the proximal end ofthe tubular-housing fluid path 32.

As shown in FIGS. 5a-5 d, these channels 30 guide fluid through theconnector along the length of the support post 28 and into thetubular-housing fluid path 32 of the Luer-lock insert 16. The maleLuer-lock insert 16 includes a tubular housing 34 having a circularcross-section. Extending upward from the center of the tubular housing34 is the support post 28. Extending downward from the center of thetubular housing 34 is a male-Luer taper 36. The tubular housing 34includes an outer shroud 38 and an inner shroud 40. The outer shroud 38surrounds the base of the support post 28 and most of the male-Luertaper 36. The portion of the outer shroud 38 surrounding the male-Luertaper 36 is internally threaded. The inner shroud 40 also surrounds thebase of the support post 28. The space between the base of the supportpost 28 and the inner shroud 40 forms an annular groove 42. As describedfurther below, the annular groove 42 is used to secure the base of theflex-tube assembly 22.

The exterior surface of the tubular housing 34 of the Luer-lock insert16 is molded to include a crown shaped outer shell 44 which includesseveral crown points 46. As shown in FIG. 6, the interior of the valvebody 12 is molded to include a crown shaped inner shell 48 whichincludes several crown points 50. The crowned tubular-housing outershell 44 of the Luer-lock insert 16 mates with the crowned valve-bodyinner shell 48 of the valve body 12, thereby facilitating snap-fitassembly of the medical connector. Alternatively, the male Luer-lockinsert 16 and valve body 12 may be joined by ultrasonic weld geometry, aspin weld, bonding, or by other means.

As is illustrated in FIGS. 7a-7 d, the interior of the valve body 12 hassections of varying diameters. The section directly adjacent the inletport 14 includes a standard ANSI Luer taper section 52 that incorporatesa very slight inward taper. The center section 54 has a larger diameterthan the taper section 52 and is separated from the taper section by thetapered ramp/lock section 56. The bottom section 58 has a largerdiameter than the center section 54 and is separated from the centersection by a taper section 60. Finally, the valve body 12 includes askirt 62. The skirt 62 has an inside diameter that is dimensioned to fitover the male Luer-lock insert 16. The valve body 12 may be molded of amaterial containing a phosphorescent colorant to render the connectorvisible in a darkened room or may be formed of a transparent material.

As shown in FIGS. 8a and 9 a, the resiliently deformable flex-tubeassembly 22 includes the flex-tube insert 24 and the flex-tube piston26. The flex-tube insert 24 is surrounded by the flex-tube piston 26. Asis shown in FIG. 14, the flex-tube assembly 22 is captured in the groove42 of the male Luer-lock insert 16 to form a tight seal about thesupport post 28 and the top of the male Luer taper 36. The flex-tubepiston 26 includes an antimicrobial agent, such as silver, silver oxideor silver sulfadiazine. The agent may be included in the materialforming the flex-tube piston or may be added to the outer surface of thepiston as a coating. These agents reduce the incidence of infection ifthe valve is not properly disinfected with an alcohol wipe prior to use.The flex-tube insert 24, valve body 12 and/or male Luer-lock 16 insertmay also include an antimicrobial agent. The peripheral surface of theflex-tube piston 26 is also lubricated with FDA approved silicone oil tofacilitate movement of the flex-tube assembly within the connector.

As shown in FIGS. 10-11b, the flex-tube insert 24 includes an annularinlet support 64, an annular outlet support 66 and a middle support 68.Positioned between adjacent supports is a collapsible section 70. Eachcollapsible section 70 includes four hinge assemblies 72 arranged in asquare, as shown in FIG. 11a. Each hinge assembly 72 includes two plates74 and a hinge 76 about which the plates pivot. As best shown in FIG.11b, the inner surfaces of the plates 74 are sloped. As explained below,the sloped surfaces prevent the plates 74 from completely collapsing oneach other. The edges 78 of the plates parallel with the hinge 76 areattached to one of the supports 64, 66, or 68. The connectionbetween-the edges 78 and the supports 64, 66, or 68 is facilitated by asupport hinge 80. Operation of the flex-tube insert 24 is describedbelow in conjunction with the flex-tube piston 26.

As shown in FIGS. 12-13b, the flex-tube piston 26 includes a piston head82, an expandable section 84 and a piston base 86. The piston head 82includes a top section 88 that is elliptical in cross-section and abottom, thick taper-lock portion 90 that is circular in cross-section.The taper-lock portion 90 includes an annular groove 92 that is sized toreceive and secure the annular inlet support (not shown) of theflex-tube insert 24. The base 86 of the flex-tube piston also includesan annular groove 94 that receives and secures the annular outletsupport (not shown). A marquise-shaped bore 96 is formed in the pistonhead 82. The top portion 88 of the piston head 82 includes a lip seal 98that comprises a pair of lips 100 that extend from opposed sides of thebore 96 to function as a seal. The bore 96, in conjunction with thehollow interior of the taper lock section 90 and the hollow interior ofthe expandable section 84, form a fluid path 102 through the flex-tubepiston 26 The piston head 82 and bore 96 are configured closeup andfunction similarly to the piston head and bore described in U.S. Pat.No. 5,676,346, inventor Karl R. Leinsing, entitled NEEDLELESS CONNECTORVALVE, and assigned to the same assignee of record of this application,the disclosure of which is hereby incorporated by reference.

Through proper selection of the dimensions of the hinge assemblies, theflex-tube insert 24 (FIG. 11a) is able to facilitate expansion of thefluid-flow path 102 (FIGS. 8a and 9 a) of flex-tube piston 26 to eitherincrease the volumetric capacity of the fluid flow path to provide apositive-bolus effect, or to maintain it at a substantially constantcapacity to provide a no-bolus effect. If desired, the flex-tubeassembly 22 may also be designed to provide a negative-bolus effect. Theflex-tube piston 26, in turn, is designed to provide a restoring forceto the flex-tube insert 24 (FIG. 11a) to return the fluid-flow path 102to a nonexpanded condition and thus return the volumetric capacity ofthe fluid flow path to its original value. To facilitate operation ofthe flex-tube assembly 22, the flex-tube piston 26 is molded of aresilient flexible rubber material such as silicone, while the flex-tubeinsert 24 is formed of a more rigid material, such as materialpolyethylene.

As shown in FIGS. 8a and 8 b, the flex-tube assembly 22 is movablebetween an uncompressed state (FIG. 8a) and a compressed state (FIG.8b). In the uncompressed state the flex-tube insert 24 has a firstmaximum width 104, as shown in FIG. 8b, and the fluid path 102 definedby the flex-tube piston 26 has a first internal volume. In thecompressed state the flex-tube insert 24 has a second maximum width 106greater than the first maximum width 104, as shown in FIG. 9b, and thefluid path 102 defined by the flex-tube piston 26 has a second internalvolume greater than or substantially equal to the first internal volume.As mentioned above, when the second internal volume is greater than thefirst internal volume a positive-bolus effect is provided. When thesecond internal volume is substantially equal to the first internalvolume a no-bolus effect is provided.

The interplay between the flex-tube insert 24 and the flex-tube piston26 facilitate the movement between the uncompressed and compressedstates. The flex-tube insert 24 is instrumental in establishing thecompressed state. Upon the application of downward force to theflex-tube assembly 22, opposed hinges 76 of the flex-tube insert 24 moveaway from each other and the respective plates 74 attached to thesehinges collapse toward each other. The sloped inner surfaces of theplates 74 limit the movement of the hinges and prevent the plates fromcompletely collapsing on each other. As the plates 74 collapse, themaximum cross section of the flex-tube insert 24 increases and theexpandible section 84 (FIG. 13a) of the flex-tube piston 26 stretches.For a positive-bolus connector this increases the internal volume of thefluid path 102 toward a second internal volume greater than the firstinternal volume. When the application of downward force is removed, theresiliency of the expandable section 84 forces the opposed hinges 76toward each other and the plates 74 apart. Thus the flex-tube assembly22 returns to its original uncompressed state and, for a positive-bolusconnector, the internal volume of the fluid path 102 decreases towardthe first internal volume. For a no-bolus connector, the internal volumeremains substantially constant as the flex-tube assembly 22 movesbetween compressed and uncompressed states.

Turning now to a more detailed description of the operation of themedical connector, with reference to FIGS. 14 and 15, the dimensions ofthe top portion 88 of the piston head 82 and the marquise-shaped bore 96are selected such that when the top portion is constrained within thecircular interior of the ANSI Luer taper section 52 the bore 96 iscompletely collapsed to tightly close off the orifice and cause theadjacent lips 100 to abut one another. The tapered shoulder 108 of thetaper lock section 90 contacts the ramp/lock section 56 of the valvebody 12 and prevents the top portion 88 of the piston head 82 fromextending beyond the inlet port 14. The internal diameter of the centersection 54 of the valve body 12 is selected such that the top portion 88of the piston head 82 is free to assume its elliptical shape whenpositioned therein. This, in turn, allows the bore 96 to reassume itsnatural marquise-shape thereby opening the fluid path 102 through theflex-tube assembly 22.

In operation of a positive-bolus medical connector, the connector 10 isinitially in its unaccessed state or closed position as shown in FIG.14. The resiliency of the expandable section 84 of the flex-tube piston26 causes the piston head 82 to be biased into the ANSI Luer tapersection 52. The shoulder 108 of the flex-tube piston 26 contacts thetapered ramp/lock section 56 of the valve body 12 and prevents the topof the piston head 82 from extending beyond the edge of the inlet port14 to form a smooth and flush surface. The bore 96 through the pistonhead 82 is tightly squeezed shut by virtue of the normally ellipticallyshaped top portion 88 of the piston head being constrained into thecircular cross-section of the ANSI Luer taper section 52. The sharppointed ends of the marquise-shaped bore 96 facilitate a tight seal uponcompression of the bore along its minor axis 110 (FIG. 13b) and bycompression of the top portion 88 of the piston head 82 along its majoraxis 112.

Just prior to accessing the connector, the top surface of the pistonhead 82 and the edge of the inlet port 14 are cleaned by, for example,passing a sterilizing swipe over the smooth surface. The absence ofridges, grooves, gaps, or protrusions ensure that proper cleanliness isachieved. The connector is then ready to be accessed by a standard maleLuer with or without a Luer lock. With reference to FIG. 15, as the maleLuer tip 114 of a male Luer connector 116 is brought into contact withthe top surface of the piston head 82, a seal is formed to preclude thepassage of liquid or air therebetween. The application of sufficientpressure causes the collapsible sections 70 of the flex-tube insert 24to collapse about the support post 28 and the expandable section 84 ofthe flex-tube piston 26 to expand. The support post 28 serves to preventthe flex-tube insert 24 from buckling and closing off the fluid path. Asthe flex-tube assembly 22 compresses, the piston head 82 moves out ofthe ANSI Luer taper section 52 and into the center section 54. As thepiston head 82 clears the tapered ramp/stop section 56 and is moved intothe center section 54, the larger internal diameter of the centersection 54 allows the top portion 88 of the piston head to assume itsnaturally elliptical open shape. This, in turn, allows the bore 96 toassume its natural marquise-shape thereby opening a fluid path throughthe piston head. Continued pressure by the male Luer tip 114 causes thebottom of the piston head 82 to communicate with the top of the supportpost 28. Fluid flows through the bore 96, into the hollow interior ofthe piston head 82, along the channels 30 formed on the outside of thesupport post 28 into the expanded areas 122 of the fluid flow path 102and then into the tubular-housing fluid path 32.

As previously mentioned, as the flex-tube assembly 22 compresses itexpands and the fluid capacity of the fluid path 102 increases, thus thevolume of fluid within the connector is greater during activation of thevalve. Because the internal volume increases during actuation, therebyproducing a partial vacuum, fluid may be drawn toward the outlet port ofthe connector, for example blood from a patient may be drawn into an IVline. The drawing of fluid at this time is beneficial in that itprovides a patency check of the IV line and ensures that infusion mayproceed.

As the male Luer is withdrawn, the restoring force generated by theexpandable section 84 of the flex-tube piston 26 causes the collapsedsections 70 of the flex-tube insert 24 to return to a noncollapsed state(FIG. 14) and the fluid capacity of the fluid path 102 decreases.Simultaneously, the elliptical top portion 88 of the piston head 82 isguided into the ANSI Luer taper section 52 by the tapered ramp/locksection 56 where it is once again forced into the constrained circularshape of the ANSI Luer taper section to close off the bore 96 andreestablish a positive seal. As the internal fluid capacity of theflex-tube assembly 22 decreases, the fluid contained therein isdisplaced. Because the bore 96 has established a positive seal at theinlet port 14, the fluid is displaced toward the outlet port 18. Thepositive displacement of fluid toward and out the outlet port 18prevents a negative-bolus effect. Essentially the change from anincreased fluid volume capacity during valve activation to a reducedfluid volume capacity during valve deactivation provides apositive-bolus effect in which a bolus of fluid is actually expelledfrom the connector 10 into the fluid line to the patient.

It is noted that the volumetric increase of the fluid path 102 duringdepression of the flex-tube assembly 22 is dependent on the depth towhich the male Luer tip 114 is inserted into the inlet port 14. As shownin FIG. 15a, as the depth of the male Luer tip increases the volumetriccapacity of the fluid path increases. At a certain depth of the maleLuer tip the volumetric capacity of the fluid path reaches a maximumvalue, beyond which the capacity begins to decrease toward a steadystate. This steady state point is reached when the male Luer tip is atits maximum depth. In one embodiment of the just-described configurationof the flex-tube assembly 22, the flex-tube assembly is dimensioned suchthat the volumetric capacity of the fluid path 102 during deactuation,i.e., the priming volume, is approximately 0.089 milliliters (ml.). Themaximum volumetric capacity during actuation is approximately 0.099 ml.

In the above-described flex-tube assembly 22, the flex-tube insert 24includes two compressible sections 70. In alternate embodiments, theflex-tube insert 24 may comprise more or fewer compressible sections 70.For example, in the connector shown in FIGS. 16-20, the flex-tube insert24 has only one compressible section 70. In this connector, the valvebody 12 and male Luer-lock insert 16 are reconfigured to accommodate theincreased second maximum cross section 106 of the flex-tube insert, asshown in FIG. 18b. Other then this difference, the remainingconfigurational and operational aspects of the connectors, including theoperation of the connectors, are substantially identical.

With reference to FIG. 21 there is shown another configuration of amedical connector which incorporates aspects of the invention. Exceptfor the flex-tube assembly, this configuration of the connector isgenerally similar to the connector of FIG. 1. Accordingly, thedescription of this connector primarily centers around the flex-tubeassembly. For ease in correlating the two configurations, the numeralsassociated with elements of the second configuration are the same asthose of the first configuration except they are primed. For numeralsthat are not primed there is no correlating element in the firstconfiguration.

As shown in FIG. 21a, the connector 10′ comprises a valve body 12′, amale Luer-lock insert 16′ and a flex-tube assembly 22′. As shown inFIGS. 22a-22 d, the male Luer-lock insert 16′ is substantially identicalto the male Luer-lock insert 16 (FIG. 5a) of the first configuration,except there is no support post 28. As shown in FIG. 23, the valve body12′ is also substantially similar to the first configuration except thatthe tapered section 60′, as shown in FIG. 24a-24 d, is slightlydifferent to accommodate for the different design of the flex-tubeassembly 22′.

As shown in FIGS. 25a-28 b, the flex-tube assembly 22′ is formed as onepiece. At the inlet end of the flex-tube assembly 22′ is an ellipticalpiston head 82′. As is shown in FIG. 29 the base 86′ is captured in thegroove 42′ between the proximal end of the male Luer taper 36′ and theinner shroud 40′ of the male Luer-lock insert 16′ to form a tight sealabout the top of the male Luer taper. The flex-tube assembly 22′ iscoated and lubricated in the same manner as previously described for thefirst configuration of the connector.

The flex-tube assembly 22′ is molded of a resilient flexible rubbermaterial, such as silicone, having various thicknesses at differentregions to provide functionality to the assembly. As shown in FIGS. 26aand 26 b, the flex-tube assembly 22′ includes an elliptical piston head82′ similar to that of the flex-tube piston of the other configuration.The flex-tube assembly 22′ also includes a piston base 86′ and a middlesupport 68′. Positioned between the piston head 82′ and the middlesupport 68′ is a collapsible/expandable section 70′. Similarly,positioned between the piston base 86′ and the middle support 68′ isanother collapsible/expandable section 70′. Each collapsible/expandablesection 70′ includes three hinge assemblies 72′ arranged in a triangle,as shown in FIG. 27a. Each hinge assembly 72′ includes two triangularplates 74′ and a hinge 76′ about which the plates pivot. The edges 78′(FIG. 26b) of the plates parallel with the hinge 76′ are attached to oneof either the bottom of the piston head 82′, the piston base 86′ or themiddle support 68′. The connection of the plate edges 78′ to the pistonhead 82′ and piston base 86′ is facilitated by a head/base hinge 80′. Asbest shown in FIG. 25, the edges 118 of the hinge assemblies 72′perpendicular to the hinges 76′ are joined to the edges of adjacenthinge assemblies by thin webs 120. The entire flex-tube assembly 22′ isformed from the same mold, thus the webs 120 are made of the samematerial as the hinge assemblies 72′ but are thinner than the hingeassemblies. For example, the thickest region of the hinge assemblyplates 74′ may be approximately 0.090 inches and the hinges 76′approximately 0.015 inches, while the thickness of the webs 120 may beapproximately 0.010 inches. This difference allows for expansion of thecollapsible/expandable section.

As shown in FIGS. 27a and 28 a, the thickness and positioning of thehinge assemblies 72′ of the flex-tube assembly 22′ are designed tofacilitate the expansion of the flex-tube assembly to either increasethe volumetric fluid capacity of the fluid flow path 102′ to provide apositive-bolus effect, or to maintain it at a substantially constantcapacity to provide a no-bolus effect. If desired, the flex-tubeassembly 22′ may also be designed to provide a negative-bolus effect.The thickness and relative positioning of the hinge assemblies 72′ andthe webs 120 in turn are designed to provide a restoring force to theflex-tube assembly 22′ to compress the flex-tube assembly and thusreturn the volumetric fluid capacity of the fluid flow path 102′ to itsoriginal value.

The flex-tube assembly 22′ is movable between an uncompressed state(FIG. 27a) and a compressed state (FIG. 28a). In the uncompressed statethe flex-tube assembly 22′ has a first maximum cross-sectional area104′, as shown in FIG. 27b, and the fluid path 102′ defined by theflex-tube assembly 22′ has a first internal volume. In the compressedstate the flex-tube assembly 22′ has a second maximum cross-sectionalarea 106′ greater than the first maximum cross sectional area 104′, asshown in FIG. 28b, and the fluid path 102′ defined by the flex-tubeassembly 22′ has a second internal volume greater than or substantiallyequal to the first internal volume. The varying thicknesses of theflex-tube assembly 22′ facilitates the movement between the uncompressedand compressed states. The thick hinge assemblies 72′ of the flex-tubeassembly 22′ are instrumental in establishing the compressed state. Uponthe application of downward force to the flex-tube assembly 22′, thehinges 76′ move outward and the respective plates 74′ attached to thesehinges collapse toward each other. As the plates 74′ collapse the webs120 stretch. For a positive-bolus connector this increases the internalvolume of the fluid path 102′ toward a second internal volume greaterthan the first internal volume. When the application of downward forceis removed, the resiliency of the hinge assemblies 72′ and the webs 120force the hinges 76′ inward and the plates 74′ apart. Thus the flex-tubeassembly 22′ returns to its original uncompressed state and for apositive-bolus connector, the internal volume of the fluid path 102′decreases. For a no-bolus connector, the internal volume remainssubstantially constant as the flex-tube assembly 22′ moves betweencompressed and uncompressed states.

Referring now to FIGS. 29 and 30, the connector 10′ is initially in itsinactive state or closed position as shown in FIG. 29. The flex-tubeassembly 22′ is pre-loaded and causes the piston head 82′ to be biasedinto the ANSI Luer taper section 52′. The top hinge plates 74′ of theflex-tube assembly 22′ contacts the taper section 60′ of the valve body12′ and prevents the top portion 88′ of the piston head 82′ fromextending beyond the edge of the inlet port 14′ to form a smooth andflush surface. The bore 96′ through the piston head 82′ is tightlysqueezed shut by virtue of the normally elliptically shaped top portion88′ of the piston head being constrained into the circular cross-sectionof the ANSI Luer taper section 52′. The sharp pointed ends of themarquise-shaped bore 96′ facilitate a tight seal upon compression of thebore along its minor axis 110′ (FIG. 26b) and compression of the pistonhead 82′ along its major axis 112′.

With reference to FIG. 30, as the male Luer tip 114′ of the male Luerconnector 116′ is brought into contact with the top surface of thepiston head 82′, the collapsible sections 70′ of the flex-tube assembly22′ collapse and expand. To prevent the flex-tube assembly 22′ frombuckling during compression, the maximum diameters of the middle support68′ and collapsible sections 70′ are sized approximately equal to thediameter of the valve body 12′. As the flex-tube assembly 22′compresses, the top portion 88′ of the piston head 82′ moves out of theANSI Luer taper section 52′ and into the taper section 60′. The largerinternal diameter of the taper section 60′ allows the top portion 88′ ofthe piston head to assume its naturally elliptical open shape. This, inturn, allows the bore 96′ to assume its natural marquise-shape therebyopening a fluid path through the piston head 82′. In this condition theconnector is in an active state or an open piston. Fluid flows throughthe bore 96′, into the hollow interior of the piston head 82′, throughthe interior of the flex-tube assembly 22′ and into the tubular-housing.fluid path 32′.

In operation of a positive-bolus medical connector, as the flex-tubeassembly 22′ compresses it expands and the fluid capacity of the fluidpath 102′ increases, thus the volume of fluid within the connectorincreases during activation of the valve. As the male Luer tip 114′ iswithdrawn, the restoring force generated by the hinge assemblies 72′ andwebs 120 cause the flex-tube assembly 22′ to return to a noncollapsedstate (FIG. 29) and the internal volume of the flex-tube assembly todecrease. Simultaneously, the elliptical top portion 88′ of the pistonhead 82′ is guided into the ANSI Luer taper section 52′ by the taperedramp/lock section 56′ where it is once again forced into the constrainedcircular shape of the ANSI Luer taper section to close off the bore 96′and reestablish a positive seal. As the internal fluid capacity of theflex-tube assembly 22′ decreases the fluid contained therein isdisplaced. Because the bore 96′ has established a positive seal at theinlet port 14′, the fluid is displaced toward the outlet port 18′. Thedisplacement of fluid toward the outlet port 18′ prevents anegative-bolus effect.

As with the first-configuration connector, the volumetric increase ofthe fluid path 102′ during depression of the flex-tube assembly 22′ isdependent on the depth to which the male Luer tip 114′ is inserted intothe inlet port 14′. In one embodiment of the second-configurationconnector, the flex-tube assembly is dimensioned such that thevolumetric capacity of the fluid path 102′ during deactuation, i.e., thepriming volume, is 0.105 ml. The maximum volumetric capacity duringactuation is greater than the priming volume.

With reference to FIG. 31, there is shown another configuration of amedical connector which incorporates aspects of the invention. Exceptfor the flex-tube assembly and the valve body, this configuration of theconnector is generally similar to the connector of FIG. 21. Accordingly,the description of this connector primarily centers around the flex-tubeassembly and the valve body. For ease in correlating the twoconfigurations, the numerals associated with elements of the thirdconfiguration are the same as those of the second configuration, exceptthey are double primed.

As shown in FIG. 31, the connector 10″ comprises a valve body 12″, amale Luer-lock insert 16″, and flex-tube assembly 22″. As shown in FIGS.32-33c the male Luer-lock insert 16″ is substantially identical to themale Luer-lock insert 16′ (FIGS. 22a-22 d) of the second configuration.As shown in FIGS. 34-35d, the valve body 12″ is also substantiallysimilar to the valve body 12′ (FIGS. 23-24d) of the secondconfiguration, except that a proportion of the tubular valve body isflattened to accommodate for the rectangular design of the flex-tubeassembly 22″. As shown in FIGS. 36-37b, the flex-tube assembly 22″ isformed similarly to the flex-tube assembly 22′ (FIGS. 25a-26 b) of thesecond configuration. At the inlet end of the flex-tube assembly 22″ isthe elliptical piston head 82″. The base 86″ is captured in the groove42″ (FIG. 33c) to form a tight seal about the top of the male-Luer taper36″. The flex-tube assembly 22″ is coated and lubricated as previouslydescribed for the second configuration. As shown in FIG. 37a, theflex-tube assembly 22″ of the third configuration includes a pair ofcollapsible/expandable sections 70″. Each collapsible/expandable section70″ includes a pair of opposed hinge assemblies 72″. Each hinge assembly72″ includes two triangular plates 74″ and a hinge 76″ about which theplates pivot.

As best shown in FIG. 36, the hinge-assemblies 72″ include beveled edges118″. The beveled edges 118″ perpendicular to the hinges 76″ are joinedto the edges of the opposite hinge assembly by a thin web 120″. Theflex-tube assembly 22″ is movable between an uncompressed state (FIG.38a) and a compressed state (FIG. 39a). In the uncompressed state theflex-tube assembly 22″ has a first maximum internal cross-sectional area104″, as shown in FIG. 38b, and the fluid path 102″ defined by theflex-tube assembly 22″ has a first internal volume. In the compressedstate the flex-tube assembly 22″ has a second maximum internalcross-sectional area 106″ greater than the first maximum internal crosssectional area 104″, as shown in FIG. 39b, and the fluid path 102″defined by the flex-tube assembly 22″ has a second internal volumegreater than or substantially equal to the first internal volume. Uponthe application of downward force to the flex-tube assembly 22″, thehinges 76″ move outward and the respective plates 74″ attached to thesehinges collapse toward each other. As the plates 74″ collapse, thebevels 118″ flatten out and the webs 120″ stretch, and for apositive-bolus connector, there is an increase in the internal volume ofthe fluid path 102″. For a no-bolus connector, the internal volumeremains substantially constant. When the application of downward forceis removed, the resiliency of the hinge assemblies 72″ and the webs 120″force the hinges 76″ inward and the plates 74″ apart. Thus the flex-tubeassembly 22″ returns to its original uncompressed state.

Other than the number of hinge assemblies 72″, the flex tube assembly22″ of the third configuration is substantially identical to theflex-tube assembly 22′ of the second configuration. In conjunction withtheir respective valve bodies 12′, 12″, the flex-tube assemblies 22′,22″ function in substantially identical ways.

Accordingly, a description of the detailed operation of the thirdconfiguration may be had by reference to the preceding description ofthe detailed operation of the second configuration.

Thus there has been shown and described a new and useful valve for usein medical connectors that provides a positive-bolus effect or ano-bolus effect while the valve is being deactuated at the inlet end.

It will be apparent from the foregoing that while particular embodimentsof the invention have been illustrated and described, variousmodifications can be made without departing from the spirit and scope ofthe invention. Accordingly, it is not intended that the invention belimited, except as by the appended claims.

What is claimed is:
 1. A method of controlling the flow of fluid betweenan inlet port and an outlet port of a medical connector having a valveassembly defining an internal fluid path having a volume, the valveassembly having an inlet end disposed within the inlet port and anoutlet end communicating with the outlet port, the inlet end carrying abore that is closed when within the inlet port and that naturally openswhen outside the inlet port, said method comprising the steps of:increasing the volume of the fluid path while opening the bore; andsubsequently decreasing the volume of the fluid path while closing thebore.
 2. The method of claim 1 wherein the valve assembly is formed of aresiliently deformable material and the step of increasing the volume ofthe fluid path while opening the bore comprises the steps of: displacingthe inlet end from the inlet port; and expanding the valve assembly in agenerally radial outward direction relative to the axis of the fluidflow path.
 3. The method of claim 2 wherein step of displacing the inletend from the inlet port comprises the step of inserting a male-Luertaper into the inlet port and applying pressure to the inlet end.
 4. Themethod of claim 3 wherein the step of decreasing the volume of the fluidpath while closing the bore comprises the steps of: placing the inletend in the inlet port; and collapsing the valve assembly in a generallyradial inward direction relative to the axis of the fluid flow path. 5.The method of claim 4 wherein the step of placing the inlet end in theinlet port comprises the step of removing the male-Luer taper from theinlet port.
 6. A method of controlling the flow of fluid between aninlet port and an outlet port of a medical connector, the medicalconnector having an internal fluid path having a volume, and having anaxially compressible valve assembly defining an internal passagewayforming part of the fluid path, the valve assembly having an inlet enddisposed within the inlet port and an outlet end communicating with theoutlet port, the inlet end carrying a bore that is closed when withinthe inlet port and that naturally opens when outside the inlet port,said method comprising the steps of: maintaining the volume of the fluidpath substantially constant while axially compressing the valve assemblyand opening the bore; and subsequently maintaining the volume of thefluid path substantially constant while axially decompressing the valveassembly and closing the bore.
 7. The method of claim 6 wherein thevalve assembly is formed of a resiliently deformable material and thestep of maintaining the volume of the fluid path substantially constantwhile axially compressing the valve assembly and opening the borecomprises the steps of: displacing the inlet end from the inlet port;and expanding the valve assembly in a generally radial outward directionrelative to the axis of the fluid flow path.
 8. The method of claim 1wherein the step of displacing the inlet end from the inlet portcomprises the step of inserting a male-Luer taper into the inlet portand applying pressure to the inlet end.
 9. The method of claim 8 whereinthe step of maintaining the volume of the fluid path substantiallyconstant while axially decompressing the valve assembly and closing thebore comprises the steps of: placing the inlet end in the inlet port;and collapsing the valve assembly in a generally radial inward directionrelative to the axis of the fluid flow path.
 10. The method of claim 9wherein the step of placing the inlet end in the inlet port comprisesthe step of removing the male-Luer taper from the inlet port.
 11. Amethod of controlling the flow of fluid between an inlet port and anoutlet port of a medical connector having a valve assembly defining aninternal fluid path having a volume, the valve assembly having an inletend disposed within the inlet port and an outlet end communicating withthe outlet port, the inlet end carrying a bore that is closed whenwithin the inlet port and opened when outside the inlet port, the valveassembly further comprising a first and a second plate, the first platebeing connected to the second plate by a hinge about which the platesare adapted to pivot, said method comprising the steps of: collapsingthe first plate towards the second plate while opening the bore, therebymoving the hinge in a generally radial outward direction relative to theaxis of the fluid flow path and increasing the volume of the fluid path;and subsequently retracting the first plate from the second plate whileclosing the bore, thereby moving the hinge in a generally radial inwarddirection relative to the axis of the fluid flow path and decreasing thevolume of the fluid path.
 12. The method of claim 11 wherein the step ofcollapsing the first plate towards the second plate while opening thebore comprises the steps of: displacing the inlet end from the inletport thereby expanding the valve assembly in a generally radial outwarddirection relative to the axis of the fluid flow path.
 13. The method ofclaim 12 wherein the step of displacing the inlet end from the inletport comprises the step of inserting a male-Luer taper into the inletport and applying pressure to the inlet end.
 14. The method of claim 13wherein the step of retracting the first plate from the second platewhile closing the bore comprises the steps of: placing the inlet end inthe inlet port thereby collapsing the valve assembly in a generallyradial inward direction relative to the axis of the fluid flow path. 15.The method of claim 14 wherein the step of placing the inlet end in theinlet port comprises the step of removing the male-Luer taper from theinlet port.
 16. A method of controlling the flow of fluid between aninlet port and an outlet port of a medical connector having an axiallycompressible valve assembly defining an internal fluid path having avolume, the valve assembly having an inlet end disposed within the inletport and an outlet end communicating with the outlet port, the inlet endcarrying a bore that is closed when within the inlet port and openedwhen outside the inlet port, the valve assembly further comprising afirst and a second plate, the first plate being connected to the secondplate by a hinge about which the plates are adapted to pivot, saidmethod comprising the steps of: collapsing the first plate towards thesecond plate while axially compressing the valve assembly and openingthe bore, thereby moving the hinge in a generally radial outwarddirection relative to the axis of the fluid flow path and maintainingthe volume of the fluid path substantially constant; and subsequentlyretracting the first plate from the second plate while axiallydecompressing the valve assembly and closing the bore, thereby movingthe hinge in a generally radial inward direction relative to the axis ofthe fluid flow path and maintaining the volume of the fluid pathsubstantially constant.
 17. The method of claim 16 wherein the step ofcollapsing the first plate towards the second plate while axiallycompressing the valve assembly and opening the bore comprises the stepsof: displacing the inlet end from the inlet port thereby expanding thevalve assembly in a generally radial outward direction relative to theaxis of the fluid flow path.
 18. The method of claim 17 wherein the stepof displacing the inlet end from the inlet port comprises the step ofinserting a male-Luer taper into the inlet port and applying pressure tothe inlet end.
 19. The method of claim 18 wherein the step of retractingthe first plate from the second plate while axially decompressing thevalve assembly and closing the bore comprises the steps of: placing theinlet end in the inlet port thereby collapsing the valve assembly in agenerally radial inward direction relative to the axis of the fluid flowpath.
 20. The method of claim 19 wherein the step of placing the inletend in the inlet port comprises the step of removing the male-Luer taperfrom the inlet port.